JP2009082371A - Radiography equipment - Google Patents

Abstract

A medical work using an implant member is shortened by making it possible to easily obtain the same-size image information regarding a portion of the subject in which the implant member is embedded.
A first radiation imaging apparatus comprising: a radiation source; and a radiation conversion panel 16 that detects radiation transmitted from the radiation source and transmitted through a subject in which an implant member is embedded in the body and converts the radiation into radiation image information. 10A, of the radiographic image information from the radiation conversion panel 16, measurement means 104 for measuring the size of the image of a part of the implant member, and an actual measurement value indicating the actual size of the part of the implant member The same-magnification image information is obtained by correcting the radiographic image information from the actual measurement value acquisition unit 106 to be acquired and the radiation image information from the radiation conversion panel 16 by the same magnification based on the measurement value from the measurement unit 104 and the acquired actual measurement value. And correction means 110.
[Selection] Figure 3

Description

  The present invention relates to a radiation imaging apparatus having a radiation source and a radiation conversion panel that detects radiation emitted from the radiation source and transmitted through a subject and converts the radiation into radiation image information.

  Conventionally, for example, radiation imaging apparatuses shown in Patent Documents 1 to 4 have been proposed as radiation imaging apparatuses including a radiation conversion panel that detects radiation emitted from a radiation source and transmitted through a subject and converts the radiation into radiation image information. Yes.

  Patent Document 1 discloses a nuclear medicine image diagnostic apparatus that can display a radioactive substance distribution image of a subject at the same position as the subject in full size. Specifically, radiation incident from a collimator provided on the back surface of the apparatus main body is detected by a semiconductor detector, the incident position is calculated and stored in sequence by a processor, and a liquid crystal display panel provided on the surface of the apparatus main body Is displayed.

  Patent Document 2 discloses an X-ray diagnostic apparatus that can output an image in actual size. The X-ray diagnostic apparatus includes an X-ray tube, a top plate, an image intensifier, a TV camera that captures an optical image from the image intensifier, and an output device 3 that outputs an image captured by the TV camera. And have. Further, an SID measurement unit for obtaining a distance (SID) from the X-ray tube to the X-ray incident surface of the image intensifier, and a distance (FSD) from the center of the subject to the X-ray incident surface of the image intensifier are obtained. And an FSD measuring unit. Then, an enlargement ratio is obtained based on these SID and FSD values, and the captured image is output in actual size. In particular, the FSD measuring unit is based on each detection value from the sensor for detecting the vertical position of the top plate and the sensor for detecting the vertical position of the image intensifier and a slight distance between the subject and the top plate. The FSD is estimated.

  Patent Document 3 discloses an X-ray imaging apparatus that can easily generate quasi-parallel X-rays capable of obtaining an image of the same magnification as a subject. In this X-ray imaging apparatus, X-rays are transmitted through a window, output, a X-ray irradiation field is limited by a diaphragm, and then incident on a flat polycapillary to obtain parallel X-rays. Parallel X-rays are irradiated onto the subject and photographed on the imaging plate. An image of the same size as the subject is obtained by imaging with parallel X-rays.

  Patent Document 4 discloses a test object measuring apparatus capable of quantitatively measuring the actual size of the measurement target portion of the test object based on image data representing the test object acquired by radiography. Yes. This test object measuring apparatus inputs image data obtained by radiographing a test object and a reference member having a known length at the same magnification, displays the image on a display screen, and displays the reference member. The positions of both ends on the image of the reference portion indicating the known length of the image are input with the input pen. Of the image of the test object displayed on the display screen, the positions of both ends on the image of the region to be measured whose length is to be measured are input with the mouse. Based on the correspondence between the length on the image between the two end positions of the reference part and the actual size between the two end positions of the reference part, the length on the image between the two end positions of the measurement target part is converted to the actual size by the calculation means. To do.

JP-A-9-311187 JP-A-7-265286 JP 2003-151895 A JP 2004-144651 A

  However, the techniques described in Patent Documents 1 and 3 have the disadvantages that the apparatus becomes large and the cost increases because it is necessary to separately provide collimator means for optically converting emitted X-rays into parallel X-rays.

  The technique described in Patent Document 2 requires FSD based on the top plate. Usually, the top plate has a problem that the standard is deviated, for example, warpage occurs because the subject needs to be supported. In addition, a fixed value set in advance as the distance between the center position of the subject and the top plate is used. Depending on the physique of the subject, the distance between the center position of the subject and the top plate may vary greatly. For this reason, the technique described in Patent Document 2 has a problem that it cannot be accurately converted to the actual size.

  On the other hand, Patent Document 4 describes a test object measuring apparatus capable of quantitatively measuring the actual size of a measurement target portion of the test object based on image data representing the test object acquired by radiography. Has been.

  The present invention has been made in consideration of such a problem, and by using the technique of Patent Document 4, it is possible to easily obtain the same-size image information regarding the site where the implant member is embedded in the subject. An object of the present invention is to provide a radiation imaging apparatus that can shorten the medical work using the implant member and can suppress an increase in size and cost of the apparatus itself.

  The radiation imaging apparatus according to the present invention includes a radiation source, and a radiation conversion panel that detects radiation transmitted from the radiation source and transmitted through a subject in which an implant member is embedded in the body and converts the radiation into radiation image information. A radiographic apparatus, comprising: measurement means for measuring the size of a part of the implant member in the radiation image information from the radiation conversion panel; and the actual size of the part of the implant member. The actual value acquisition means for acquiring the actual measurement value indicating the radiation image information from the radiation conversion panel, and the same-magnification image by correcting the radiographic image information from the measurement means based on the measurement value from the measurement means and the acquired actual measurement value It has the equal magnification correction means used as information.

  Accordingly, it is possible to easily obtain the same-size image information regarding the portion of the subject in which the implant member is embedded, and to shorten the medical work using the implant member. Increase in size and cost can be suppressed.

  In the present invention, the equal-magnification image information obtained by the equal-magnification correcting unit may be equal-magnification image information related to a portion of the subject in which the implant member is embedded.

  Moreover, in this invention, you may make it the said measured value acquisition means acquire from a database based on the identification number of the said implant member.

  Further, in the present invention, the measurement means includes calculation means for calculating the size of the partial image of the implant member based on a projection coordinate system on the radiation conversion panel, and the implant member to the subject. A means for acquiring a standard attachment angle of the implant member based on information on the attachment site of the device, and a correction means for correcting the value obtained by the calculation means based on the acquired attachment angle. It may be.

  Further, in the present invention, the measurement unit includes a first calculation unit that calculates the size of the partial image of the implant member based on a projection coordinate system on the radiation conversion panel, and the subject to the subject. Means for acquiring a standard attachment angle of the implant member based on information of a mounting site of the implant member, and the actual measurement value acquisition means includes the three-dimensional image of the same member as the implant member. You may make it have the 2nd calculating means which calculates the magnitude | size of the image which rotated the image corresponding to a one part image based on the said attachment angle based on a screen coordinate system.

  In the present invention, furthermore, a distance measuring means for measuring a separation distance from the radiation source to the radiation conversion panel, and a relative distance from a position of the radiation conversion panel to a position to be a reference position of the subject. A second equal-magnification correction that obtains equal-magnification image information related to the reference position of the subject based on the relative distance acquisition unit to be acquired, the measurement value obtained by the measurement unit, the separation distance, and the relative distance. Means may be included.

  As described above, according to the radiographic apparatus according to the present invention, it is possible to easily obtain the same-size image information related to the site where the implant member is embedded in the subject, and the medical work using the implant member. As well as an increase in size and cost of the device itself.

  Embodiments of the radiation imaging apparatus according to the present invention will be described below with reference to FIGS.

  First, as shown in FIG. 1, a radiation imaging apparatus according to the first embodiment (hereinafter referred to as a first radiation imaging apparatus 10A) is emitted from a radiation source 12, and the radiation source 12, and is implanted into the body. A radiation conversion panel 16 that detects radiation transmitted through the subject 14 in which the member 13 is embedded, and converts the radiation into radiation image information; and one or more databases 18A, 18B, ... in which various tables and image data are registered; It has an image memory 20 for storing radiation image information, and a computer 22 for controlling various means.

  The radiation conversion panel 16 is accommodated in the casing of the cassette 24. An indicator 26 indicating the installation position of the radiation conversion panel 16 is displayed on the side surface of the casing. Accordingly, when the cassette 24 is set in the first radiation imaging apparatus 10A, the position of the radiation conversion panel 16 can be easily recognized by the index 26 displayed on the side surface of the casing.

  As shown in FIG. 2, the radiation conversion panel 16 includes a thin film transistor (TFT) made of a photoelectric conversion layer 51 made of a material such as amorphous selenium (a-Se) that senses radiation and generates charges. After the generated charge is stored in the storage capacitor 53, the TFT 52 is sequentially turned on for each row, and the charge is read as an image signal. In FIG. 2, only the connection relationship between one pixel 50 including the photoelectric conversion layer 51 and the storage capacitor 53 and one TFT 52 is shown, and the configuration of the other pixels 50 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to arrange a means for cooling the radiation conversion panel 16 in the cassette 24.

  A gate line 54 extending parallel to the row direction and a signal line 56 extending parallel to the column direction are connected to the TFT 52 connected to each pixel 50. Each gate line 54 is connected to a line scanning drive unit 58, and each signal line 56 is connected to a multiplexer 66 constituting a reading circuit.

  Control signals Von and Voff for controlling on / off of the TFTs 52 arranged in the row direction are supplied from the line scanning drive unit 58 to the gate line 54. In this case, the line scan driving unit 58 includes a plurality of first switches SW1 that switch the gate lines 54, and a row address decoder 60 that outputs a selection signal for selecting one of the first switches SW1. The row address decoder 60 is supplied with an address signal from the cassette control unit 46.

  In addition, the charge held in the storage capacitor 53 of each pixel 50 flows out to the signal line 56 through the TFTs 52 arranged in the column direction. This charge is amplified by the amplifier 62. A multiplexer 66 is connected to the amplifier 62 via a sample and hold circuit 64. The multiplexer 66 includes a plurality of second switches SW2 for switching the signal lines 56, and a column address decoder 68 for outputting a selection signal for selecting one of the second switches SW2. An address signal is supplied from the cassette control unit 46 to the column address decoder 68. An A / D converter 70 is connected to the multiplexer 66, and radiation image information converted into a digital signal by the A / D converter 70 is output via the cassette control unit 46, and the image memory 20 is output via the computer 22. Will be remembered.

  As shown in FIG. 3, the first radiation imaging apparatus 10 </ b> A includes a data storage unit 102 that stores radiation image information from the radiation conversion panel 16 in the first storage area 100 of the image memory 20, and the radiation conversion panel 16. Measurement means 104 for measuring the size of a part of the image of the implant member 13, and actual measurement value acquisition means for acquiring an actual measurement value indicating the actual size of the part of the implant member 13. 106, the radiation image information from the radiation conversion panel 16 is subjected to the same magnification correction based on the measurement value from the measurement unit 104 and the actual measurement value acquired by the actual measurement value acquisition unit 106 to obtain the same magnification image information, The same-magnification correcting means 110 for storing the same-size image information in the second storage area 108 of the image memory 20 and the radiation image information from the first storage area 100 of the image memory 20 are read. A first output unit 116 for outputting to the printer 112 and the monitor 114; and a second output unit 118 for reading out the same-size image information from the second storage area 108 of the image memory 20 and outputting the same to the printer 112 and the monitor 114. .

  Note that the configuration of the first radiation imaging apparatus 10A includes a first method for imaging with the subject 14 standing and a second method for imaging with the subject 14 lying down. In the first method, as shown in FIG. 1, the cassette 24 is attached to a standing imaging stand 140 with its imaging surface (imaging surface of the radiation conversion panel 16) vertical. Then, the subject 14 stands facing the imaging surface of the cassette 24 attached to the imaging stand 140, and the radiation source 12 is installed facing the subject 14. In this case, the radiation source 12 and the imaging table 140 can be moved in a direction (left-right direction) that approaches and separates from each other by known moving mechanisms 142 and 144, respectively. In the second method, as shown in FIG. 4, the subject 14 lies on the top 146, and the cassette 24 is set on the imaging table 140 installed below the top 146. Then, the top plate 146 is positioned facing the imaging surface of the cassette 24, and the radiation source 12 is installed facing the top plate 146. Also in this case, the radiation source 12 and the imaging stand 140 are movable in a direction (vertical direction) approaching and separating from the imaging surface of the cassette 24 by known moving mechanisms 142 and 144, respectively.

  As shown in FIG. 3, the actual measurement value acquisition unit 106 acquires the actual measurement value of the implant member 13 from the first database 18 </ b> A based on the identification number of the implant member 13 embedded in the subject 14. In the first database 18A, a first information table 150 is arranged for each implant member 13 to be used, and the corresponding first information table 150 is read using the identification number of the implant member 13 as a search key, and the read first information table An actual measurement value of the corresponding implant member 13 is acquired from 150.

  As an actual measurement value of the implant member 13, for example, as shown in FIG. 5, when the shape of one implant member 13 is, for example, a shape in which a rectangular body 154 is integrated with a plate member 152 (actually complicated The long side D1, the short side D2, the thickness T of the plate member 152, the long side d1, the short side d2, the diagonal L, and the thickness t of the rectangular body 154 are applicable. To do. As will be described later, which dimension is used is determined by a partial image designated by the coordinate input device 156 such as a mouse among the images of the implant member 13 included in the radiation image information. This determination can be made by displaying the contents of the first information table 150 corresponding to the implant member 13 on the monitor 114, and the doctor or the radiation technician in charge performs a selection operation with the coordinate input device 156 such as a mouse. . The determined actual measurement value is supplied to the equal magnification correction means 110.

  As shown in FIG. 6, the measurement unit 104 calculates the length of the range specified by the coordinate input device 156 such as a mouse among the radiation image information stored in the first storage area 100 of the image memory 20. And a calculating means 158. For example, as shown in FIG. 7, the length of the range specified by the coordinate input device 156 is a part of the image of a part of the implant member 13 embedded in the subject 14 in the radiographic image information displayed on the monitor 114. It is the length of both ends (one end 160a and the other end 160b) whose dimensions are determined in advance. FIG. 7 shows a case where both ends of the diagonal line in the image of the rectangular body 154 are designated and the length L of the diagonal line is measured.

  However, the length of the range specified here is the length based on the radiation image information stored in the image memory 20, that is, the length in the screen coordinate system (the projected image on the imaging surface of the radiation conversion panel 16). Based on the length). Therefore, as shown in FIG. 8A, the implant member 13 is embedded so that the designated diagonal line (the line segment designated by the one end 160a and the other end 160b) is parallel to the imaging surface 16a of the radiation conversion panel 16. If there is no problem, as shown in FIG. 8B, if the implant member 13 is embedded so that the designated diagonal line is not parallel to the imaging surface 16a of the radiation conversion panel 16 (oblique direction). An error will occur.

  Therefore, the measurement unit 104 is obtained by the angle acquisition unit 162 that acquires the standard attachment angle θ of the implant member 13 and the calculation unit 158 based on the information on the attachment site of the implant member 13 to the subject 14. Correction means 164 for correcting the value based on the acquired mounting angle θ.

  The standard attachment angle θ is not an actually measured value when the implant member 13 is actually attached to the subject 14, but an attachment angle (optimum attachment) for each part described in the manual regarding the attachment of the implant member 13. Angle). In particular, the attachment angle θ is not an angle in a plane parallel to the imaging surface 16a of the radiation conversion panel 16, but an angle along a direction perpendicular to the imaging surface 16a of the radiation conversion panel 16.

  In the second database 18B, a second information table 165 relating to the mounting angle θ is arranged for each implant member 13 used. Therefore, the angle acquisition unit 162 reads the corresponding second information table 165 using the identification number of the implant member 13 as a search key, and acquires the attachment angle θ corresponding to the attachment site from the read second information table 165. Also in this case, the content of the searched second information table 165, that is, the mounting angle θ for each mounting site of the corresponding implant member 13 is displayed on the monitor 114, and the doctor or the radiologist in charge uses the coordinate input device 156. The mounting angle θ can be determined by selecting the mounting site. The determined mounting angle θ is supplied to the correction means 164.

The correction unit 164 corrects the value obtained by the calculation unit 158 based on the mounting angle θ from the angle acquisition unit 162. Specifically, when the length of the projection coordinate system of the radiation conversion panel 16 of a part of the image is x, the corrected length is L, and the mounting angle is θ, correction is performed by performing the following calculation. The corrected value is supplied to the equal magnification correction means 110.
L = x / cos θ

The equal magnification correction unit 110 reduces the radiation image information from the radiation conversion panel 16 based on the measurement value (corrected value) from the measurement unit 104 and the actual measurement value acquired by the actual measurement value acquisition unit 106. Calculate the rate. The reduction rate can be obtained by the following relational expression.
Reduction ratio = actual value / measured value (value after correction)

  By multiplying the reduction ratio in the vertical direction and the horizontal direction of the radiation image information, the same-size image information is obtained.

  The same-size image information related to the site where the implant member 13 is embedded in the subject 14 is output to the printer 112 by the second output unit 118 or displayed on the monitor 114.

  Next, the operation of the first radiation imaging apparatus 10A will be described.

  First, the cassette 24 is set on the imaging stand 140, the subject 14 is positioned facing the imaging surface of the cassette 24, and the radiation source 12 is installed facing the subject 14.

  The doctor or the responsible radiographer operates the irradiation switch to perform radiography of the subject 14. By this imaging, the radiation transmitted through the subject 14 in which the implant member 13 is embedded in the body is converted into radiation image information by the radiation conversion panel 16, read into the computer 22, and stored in the first storage area 100 of the image memory 20. Stored.

  The radiation image information stored in the first storage area 100 is output to the printer 112 by the first output means 116 or displayed on the monitor 114.

  At this time, the doctor or the radiologist in charge uses the coordinate input device 156 to specify both ends (for example, both ends of the diagonal line) in the partial image of the implant member 13 in the radiographic image information displayed on the monitor 114. To do. Based on this designation, the calculation means 158 of the measurement means 104 measures the lengths at both ends and supplies the measurement results to the correction means 164.

  Thereafter, the doctor or the radiologist in charge inputs the identification number of the implant member 13 using an input device such as a keyboard.

  The actual measurement value acquisition unit 106 reads the first information table 150 of the corresponding implant member 13 from the first database 18A based on the input identification number. The contents of the read first information table 150 (dimensions of each part of the implant member 13) are displayed on the monitor 114. The doctor or the radiation technician in charge uses the coordinate input device 156 to specify the dimensions of the part specified this time from the contents of the displayed first information table 150. The designated dimension (actual value) is held in a register or the like.

  The angle acquisition unit 162 of the measurement unit 104 reads the second information table 165 related to the mounting angle θ of the corresponding implant member 13 from the second database 18B based on the input identification number. The content of the read second information table 165 (attachment angle θ for each attachment site of the implant member 13) is displayed on the monitor 114. The doctor or the radiation technician in charge uses the coordinate input device 156 to specify the mounting angle θ corresponding to the mounting site specified this time from the contents of the displayed second information table 165. The designated mounting angle θ is supplied to the correction means 164.

  The correction unit 164 corrects the value obtained by the calculation unit 158 based on the mounting angle from the angle acquisition unit 162. The corrected value is held in a register or the like.

  In the present embodiment, a correction execution switch 166 (see FIG. 6) for executing the equal magnification correction is further arranged on the console. By operating the correction execution switch 166, the equal magnification correction unit 110 is activated to read out the radiographic image information from the image memory 20, and the radiographic image information is used as a measurement value (corrected value) from the measurement unit 104. Based on the actual measurement value acquired by the actual measurement value acquisition unit 106, the same-magnification correction is performed to obtain the same-magnification image information. This equal-magnification image information is equal-magnification image information related to a portion of the subject 14 in which the implant member 13 is implanted, and is stored in the second storage area 108 of the image memory 20.

  The same-size image information stored in the second storage area 108 of the image memory 20 is output to the printer 112 or displayed on the monitor 114 by the second output means 118.

  As described above, in the first radiographic apparatus 10A, it is possible to easily obtain the same-size image information regarding the site where the implant member 13 is embedded in the subject 14, and the medical work using the implant member 13 can be performed. Shortening can be achieved.

  Next, a radiation imaging apparatus (hereinafter referred to as a second radiation imaging apparatus 10B) according to a second embodiment will be described with reference to FIGS. 9 to 10B.

  The second radiation imaging apparatus 10B has substantially the same configuration as the first radiation imaging apparatus 10A described above, but the configurations of the measurement unit 104 and the actual measurement value acquisition unit 106 are different as shown in FIG.

  The measurement unit 104 includes a calculation unit 158 (having the same configuration as the calculation unit 158 described above) that calculates the size of a part of the image of the implant member 13 based on a projection coordinate system on the radiation conversion panel 16.

  The actual measurement value obtaining unit 106 obtains a standard attachment angle θ of the implant member 13 on the basis of information on the site where the implant member 13 is attached to the subject 14 (the same as the angle obtaining unit 162 described above). The size of an image obtained by rotating an image corresponding to a part of the three-dimensional image of the same member as the implant member 13 embedded in the subject 14 based on the attachment angle θ. Second calculation means 168 for calculating based on the system is included.

  That is, the second computing means 168 acquires and displays a three-dimensional image of the same member as the implant member 13 embedded in the subject 14 on the monitor 114 from the third database 18C. The third database 18C stores a three-dimensional image 170 for each implant member 13 to be used, and the second calculation means 168 reads out the corresponding three-dimensional image 170 using the identification number of the implant member 13 as a search key. Displayed on the monitor 114. At this time, for example, as shown in FIG. 10A, the display is performed so that the front surface of the rectangular body 172 that is the target as a partial image faces the screen surface (image memory 20). When viewed in the world coordinate system, the front surface of the rectangular body 172 and the screen surface are displayed in parallel. Then, the three-dimensional image 170 is rotated by the mounting angle θ acquired by the angle acquisition unit 162 of the actual measurement value acquisition unit 106. By this rotation operation, the front surface of the rectangular body 172 is rotated by the attachment angle θ, and is almost in the same state as the implant member 13 embedded in the subject 14. That is, the attachment state of the implant member 13 with respect to the imaging surface of the radiation conversion panel 16 and the arrangement state of the three-dimensional image 170 with respect to the screen surface are substantially the same.

  Accordingly, by measuring the length of the diagonal line of the rectangular body 172 in the projected image of the three-dimensional image 170 on the screen surface, an actual measurement value corresponding to the diagonal line of the projected image of the rectangular body 154 on the implant member 13 can be obtained. become.

Then, the equal magnification correcting unit 110 is connected to the radiation conversion panel 16 based on the measured value from the calculating unit 158 of the measuring unit 104 and the actually measured value calculated by the second calculating unit 168 of the actually measured value acquiring unit 106. The reduction rate of the radiation image information is calculated. The reduction rate can be obtained by the following relational expression.
Reduction ratio = actual value / measured value

  By multiplying the reduction ratio in the vertical direction and the horizontal direction of the radiation image information, the same-size image information is obtained.

  The same-size image information related to the site where the implant member 13 is embedded in the subject 14 is output to the printer 112 by the second output unit 118 or displayed on the monitor 114.

  As described above, in the second radiographic apparatus 10B, the implant member that is artificially embedded in the subject 14 by rotating the three-dimensional image 170 of the same member as the implant member 13 based on the acquired attachment angle θ. 13 so as to obtain an actual measurement value, it is possible to easily obtain the same-size image information regarding the portion of the subject 14 in which the implant member 13 is implanted. The used medical work can be shortened.

  Next, a radiation imaging apparatus (hereinafter referred to as a third radiation imaging apparatus 10C) according to a third embodiment will be described with reference to FIGS.

  This third radiation imaging apparatus 10C has substantially the same configuration as that of the first radiation imaging apparatus 10A described above. However, in addition to the same-size image information regarding the portion of the subject 14 in which the implant member 13 is implanted, It is different in that it is configured so that the same-size image information regarding the set part can be obtained.

  That is, the third radiation imaging apparatus 10C includes a distance measuring unit 174 that measures the separation distance from the radiation source 12 to the radiation conversion panel 16, and the position of the subject 14 from the position of the radiation conversion panel 16, as shown in FIG. Based on the relative distance acquisition means 176 for acquiring the relative distance to the reference position, the measurement value, the separation distance, and the relative distance, the second same-size image information related to the reference position of the subject 14 is obtained. The second same-size image information is read out from the second storage unit 178 of the image memory 20 and the second same-size correction unit 180 that stores the second same-size image information in the third storage region 178 of the image memory 20. And a third output unit 182 for outputting to the printer 112 and the monitor 114.

  Note that the measurement unit 104 and the actual measurement value acquisition unit 106 are the same as the measurement unit 104 and the actual measurement value acquisition unit 106 in the first radiation imaging apparatus 10 </ b> A, and thus redundant description thereof is omitted.

  The distance measuring means 174 has, for example, a first position sensor 184 such as a rotary encoder that measures the amount of movement of the radiation source 12, and a second position sensor 186 such as a rotary encoder that measures the amount of movement of the imaging table 140, for example. Then, the distance from the radiation source 12 to the radiation conversion panel 16 is measured based on the detection values from the first position sensor 184 and the second position sensor 186.

  The relative distance acquisition unit 176 acquires the relative distance input by the input device 188 such as a keyboard. In this case, the relative distance may be an arbitrary value, but preferably the distance from the position of the radiation conversion panel 16 of the cassette 24 set in the third radiation imaging apparatus 10C to an arbitrary position on the side surface of the subject 14 is selected. . A position indicated by the relative distance on the side surface of the subject 14 is set as a reference position.

  Of course, there is a case where a part corresponding to a human shoulder bone is empirically used as a reference position. In this case, a distance from the position of the radiation conversion panel 16 to a part corresponding to the shoulder bone of the subject 14 is measured. The actual measurement value may be used as the relative distance.

  First, the second equal magnification correction unit 180 first obtains a virtual size (for example, a virtual length of a diagonal line of the rectangular body 154) at a relative distance of a partial image of the implant member 13 as follows. Here, the virtual size is referred to as a virtual length.

  That is, as shown in FIG. 12, the first base 190 having the length L indicated by the measurement value from the measuring means 104 (the length L of the diagonal line of the rectangular body 154 at the separation distance m) and the radiation source 12 are apexes P. A first triangle 192A, a second base 194 having a virtual length k at a relative distance n, and a second triangle 192B having the radiation source 12 as a vertex P are assumed, and the first triangle 192A and the second triangle 192B are similar to each other. .

Therefore, the virtual length k at the relative distance n can be obtained by calculating the following relational expression.
Virtual length k = (separation distance m−relative distance n) × measured value L / separation distance m

Then, the second equal magnification correction unit 180 calculates the reduction rate of the radiation image information from the radiation conversion panel 16 based on the measurement value from the measurement unit 104 and the virtual length k obtained as described above. . The reduction rate can be obtained by the following relational expression.
Reduction rate = virtual length / measured value

  By multiplying the reduction ratio by the vertical direction and the horizontal direction of the radiographic image information, second equal-magnification image information is obtained.

  Of the subject 14, the second equal-size image information related to the reference position of the subject 14 is output to the printer 112 by the third output unit 182 or displayed on the monitor 114.

  As described above, in the third radiation imaging apparatus 10C, based on the radiographic image information obtained once, the same-size image information related to the site where the implant member 13 is implanted and the reference position of the subject 14 (for example, on the shoulder bone) Second equal-magnification image information on the corresponding part) can be obtained, and shortening of the medical work using the radiation imaging apparatus can be effectively achieved.

  Of course, the radiographic apparatus according to the present invention is not limited to the above-described embodiment, and various configurations can be adopted without departing from the gist of the present invention.

It is a block diagram which shows an example of a 1st radiography apparatus roughly. It is a circuit diagram which shows one structural example of a radiation conversion panel. It is a functional block diagram which shows the control system of a 1st radiography apparatus. It is a block diagram which shows schematically the other example of a 1st radiography apparatus. It is a perspective view which shows an example of the implant member embedded in a subject. It is a functional block diagram which shows the structure of the measurement means of a 1st radiography apparatus. It is explanatory drawing which shows the example which designates the magnitude | size of the one part image of an implant member among radiographic image information. FIG. 8A is an explanatory diagram showing a case where the designated diagonal is parallel to the imaging surface of the radiation conversion panel, and FIG. 8B shows a case where the designated diagonal is not parallel to the imaging surface of the radiation conversion panel. It is explanatory drawing. It is a functional block diagram which shows the structure of the measurement means and measured value acquisition means of a 2nd radiography apparatus. FIG. 10A is an explanatory diagram illustrating a state in which a three-dimensional image is displayed on a monitor, and FIG. 10B is an explanatory diagram illustrating a state in which the three-dimensional image is rotated by an attachment angle. It is a functional block diagram which shows the control system of a 3rd radiography apparatus. It is explanatory drawing which shows one method of calculating | requiring the virtual length corresponding to the relative distance of the line segment of a measuring object.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10A-10C ... Radiography apparatus 12 ... Radiation source 13 ... Implant member 14 ... Subject 16 ... Radiation conversion panel 18A-18C ... Database 20 ... Image memory 22 ... Computer 24 ... Cassette 104 ... Measurement means 106 ... Actual value acquisition means 110 ... Same magnification correction means 158 ... Calculation means 162 ... Angle acquisition means 164 ... Correction means 168 ... Second calculation means 174 ... Distance measurement means 176 ... Relative distance acquisition means 180 ... Second equal magnification correction means

Claims (6)

A radiation source;
A radiation imaging apparatus having a radiation conversion panel that detects radiation emitted from the radiation source and transmitted through a subject in which an implant member is embedded in the body, and converts the radiation into radiation image information,
Among the radiation image information from the radiation conversion panel, a measuring unit that measures the size of a part of the image of the implant member;
Actual value acquisition means for acquiring an actual value indicating the actual size of the part of the implant member;
The radiographic image information from the radiation conversion panel includes a measurement value from the measurement unit and an equal magnification correction unit that performs an equal magnification correction based on the acquired actual measurement value to obtain an equal magnification image information. Radiation imaging device. The radiographic apparatus according to claim 1,
The radiographic apparatus according to claim 1, wherein the equal-magnification image information obtained by the equal-magnification correcting unit is equal-magnification image information related to a portion of the subject in which the implant member is embedded. The radiographic apparatus according to claim 1,
The measured value acquisition means acquires from a database based on an identification number of the implant member. The radiographic apparatus according to claim 1,
The measuring means includes
A computing means for computing the size of the image of the part of the implant member based on a projection coordinate system to the radiation conversion panel;
Means for obtaining a standard attachment angle of the implant member based on information on a site where the implant member is attached to the subject;
A radiation imaging apparatus, comprising: a correction unit that corrects a value obtained by the calculation unit based on the acquired attachment angle. The radiographic apparatus according to claim 1,
The measurement means includes first calculation means for calculating the size of the partial image of the implant member based on a projection coordinate system to the radiation conversion panel;
Means for acquiring a standard attachment angle of the implant member based on information on a mounting site of the implant member to the subject;
The measured value acquisition means calculates, based on a screen coordinate system, the size of an image obtained by rotating an image corresponding to the part of the three-dimensional image of the same member as the implant member based on the attachment angle. A radiation imaging apparatus comprising: a second computing unit that performs the following. The radiographic apparatus according to claim 1,
Furthermore, distance measuring means for measuring a separation distance from the radiation source to the radiation conversion panel;
A relative distance acquisition means for acquiring a relative distance from a position of the radiation conversion panel to a position to be a reference position of the subject;
A second equal-magnification correcting unit that obtains equal-magnification image information related to the reference position of the subject based on the measurement value obtained by the measuring unit, the separation distance, and the relative distance; Radiography equipment.

Images